US20200038870A1 - Microfluidic device, microfluidic system and method for the isolation of particles - Google Patents
Microfluidic device, microfluidic system and method for the isolation of particles Download PDFInfo
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- US20200038870A1 US20200038870A1 US16/342,923 US201716342923A US2020038870A1 US 20200038870 A1 US20200038870 A1 US 20200038870A1 US 201716342923 A US201716342923 A US 201716342923A US 2020038870 A1 US2020038870 A1 US 2020038870A1
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
- B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
- B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
- B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
- B01L3/502761—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip specially adapted for handling suspended solids or molecules independently from the bulk fluid flow, e.g. for trapping or sorting beads, for physically stretching molecules
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/06—Fluid handling related problems
- B01L2200/0647—Handling flowable solids, e.g. microscopic beads, cells, particles
- B01L2200/0652—Sorting or classification of particles or molecules
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
- B01L2200/06—Fluid handling related problems
- B01L2200/0684—Venting, avoiding backpressure, avoid gas bubbles
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/06—Auxiliary integrated devices, integrated components
- B01L2300/0627—Sensor or part of a sensor is integrated
- B01L2300/0663—Whole sensors
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2300/00—Additional constructional details
- B01L2300/08—Geometry, shape and general structure
- B01L2300/0809—Geometry, shape and general structure rectangular shaped
- B01L2300/0816—Cards, e.g. flat sample carriers usually with flow in two horizontal directions
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
- B01L2400/0415—Moving fluids with specific forces or mechanical means specific forces electrical forces, e.g. electrokinetic
- B01L2400/0424—Dielectrophoretic forces
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
- B01L2400/043—Moving fluids with specific forces or mechanical means specific forces magnetic forces
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
- B01L2400/00—Moving or stopping fluids
- B01L2400/04—Moving fluids with specific forces or mechanical means
- B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
- B01L2400/0433—Moving fluids with specific forces or mechanical means specific forces vibrational forces
- B01L2400/0436—Moving fluids with specific forces or mechanical means specific forces vibrational forces acoustic forces, e.g. surface acoustic waves [SAW]
Definitions
- the present invention concerns a microfluidic device, a microfluidic system and a method for isolating particles of a sample, in particular a biological sample.
- Systems for the isolation of particles of at least one specific type of a sample, in particular a biological sample in liquid form are known. These systems receive, in use, a sample comprising particles of the specific type and typically particles of one or more different types and are adapted to select and separate the particles of the specific type and the particles of the different type or types. Generally, these systems allow not only the isolation of the particles of the specific type belonging to a sample comprising also other types of particles, but also recognition of the various particles before their isolation.
- tumour cells comprising tumour cells, foetal cells, stem cells or other types of cells.
- a system of this type is described in EP-A-2408562 and comprises an analysis apparatus and a microfluidic device (in particular, a cartridge) for isolation of the particles of the specific type.
- microfluidic device for the isolation of particles which is of the disposable type, is, in use, housed in the apparatus in a removable manner.
- the microfluidic device is provided with a first inlet through which, in use, a sample comprising the particles is introduced into the microfluidic device, a separation unit, which comprises a main chamber and a recovery chamber fluidically connected to each other, and an inlet duct connected to the first inlet and to the main chamber.
- the particles of the specific type are transferred, in a selective manner with respect to particles of a different type, into the recovery chamber, which comprises a waiting area and a recovery area.
- the device further comprises an outlet connected by means of an outlet duct to the recovery chamber, more specifically to the recovery area.
- the particles of the specific type are discharged from the recovery chamber, more specifically from the recovery area and from the microfluidic device, through the first duct and the outlet.
- the microfluidic device also comprises a second inlet, which is connected by means of a feeding duct to the recovery chamber and through which, in use, a flushing liquid is introduced into the recovery chamber.
- the microfluidic device further comprises a collection reservoir connected to the main chamber and to the waiting area.
- a hydrophobic membrane is also provided arranged at a terminal portion of the collection reservoir, said membrane allowing outflow of the air present in the microfluidic device and, when intact, preventing outflow of the sample or of parts of the sample and/or of the sample.
- the apparatus comprises a first pump, which is adapted to direct the sample through the inlet duct into the separation unit, and a second pump, which is adapted to direct the flushing liquid into the recovery chamber.
- the system further comprises a recognition device having a fluorescence microscope, which allows the recognition of the types of particles and the determination of the relative positions, and an actuator device, which allows the particles to be moved according to the type of particles recognised by the recognition device so as to convey the particles of the specific type into the recovery chamber and maintain the particles of different type in the main chamber. More specifically, the actuator device is adapted to displace the particles by means of dielectrophoresis.
- a microfluidic system of this type is described in EP-A-2408562 and does not allow (or allows only to a limited extent) the introduction of several successive portions of the sample into the separation unit.
- a further drawback lies in the fact that a malfunction of the hydrophobic membrane (for example a rupture) can cause outflow of the sample from the microfluidic device, which may damage the apparatus and/or the system.
- the object of the present invention is to provide a microfluidic device, a microfluidic system and a method for the isolation of particles which overcome, at least partially, the drawbacks of the known art and are, at the same time, easy and inexpensive to produce.
- a microfluidic device a microfluidic system and a method for the isolation of particles are provided, as claimed in the following independent claims and, preferably, in any one of the claims depending directly or indirectly on the independent claims.
- equivalent diameter of a section we mean the diameter of a circle having the same area as the section.
- microfluidic system we mean a system comprising at least one microfluidic duct and/or at least one microfluidic chamber.
- the microfluidic system comprises at least one pump (more specifically, a plurality of pumps), at least one valve assembly (more specifically, a plurality of valve assemblies) and if necessary at least one gasket (more specifically, a plurality of gaskets).
- a reservoir can comprise a microfluidic duct, a microfluidic chamber or any combination thereof.
- microfluidic duct we mean a duct having a section with an equivalent diameter smaller than 0.5 mm.
- the microfluidic chamber has a height of less than 0.5 mm. More specifically, the microfluidic chamber has a width and a length greater than the height (more precisely at least five times the height).
- particle we mean a corpuscle having its largest dimension of less than 500 ⁇ m (advantageously less than 150 ⁇ m).
- particles are: cells, cell debris (in particular, cell fragments), cell aggregates (e.g. small clusters of cells deriving from stem cells like neurospheres or mammospheres), bacteria, lipospheres, microspheres (in polystyrene and/or magnetic), complex nanospheres (e.g. nanospheres up to 100 nm) formed of microspheres bound to cells.
- the particles are cells.
- the largest dimension of the particles is smaller than 60 ⁇ m.
- the dimensions of the particles can be measured in a standard way by microscopes with a graduated scale or normal microscopes used with slides (on which the particles are deposited) with a graduated scale.
- dimensions of a particle we mean the length, width and thickness of the particle.
- a movement or other analogous terms indicating a movement and/or a separation and/or a displacement
- a movement or other analogous terms indicating a movement and/or a separation and/or a displacement
- which is substantially selective entails moving particles with at least 90% (advantageously 95%) of particles of specific type/s (percentage given by the number of particles of the specific type/s with respect to the number of overall particles).
- FIG. 1 schematically illustrates a system produced according to the present invention
- FIG. 2 is a view from above of a device of the system of FIG. 1 ;
- FIG. 3 is a view from above of an exploded drawing of the device of FIG. 2 ;
- FIG. 4 is a view from below of an exploded drawing of the device of FIG. 2 ;
- FIG. 5 is an enlarged view of a detail of FIG. 4 .
- number 1 indicates schematically and overall a microfluidic system 1 for the isolation of particles of at least one specific type belonging to a sample C 1 .
- the system 1 comprises a microfluidic device 2 for the isolation of the particles of the specific type and an apparatus 3 (only partially illustrated) adapted to house the device 2 , in particular in a removable manner, and to cooperate with the device 2 for isolation of the particles of specific type.
- the system 1 is adapted to isolate a specific type of particle.
- the system 1 can also be used for the isolation of different types of particles.
- the sample typically comprises the particles of the specific type and at least one other type of particle. More precisely, the sample is a biological sample and, in particular, is a suspension of biological cells (for example cells).
- the system 1 is adapted to isolate the particles of the specific type in a substantially selective manner with respect to the particles of the other type or other types. More specifically, the system 1 is adapted to isolate the particles of the specific type from the other type of particles so as to obtain a final sample C 2 adapted to be further analysed, in particular by means of biological analysis.
- the device 2 is a disposable cartridge.
- the device 2 comprises:
- the chamber 7 of the unit 5 comprises a waiting area 7 a and a recovery area 7 b fluidically connected to each other and to the chamber 6 .
- the area 7 b is fluidically connected, in particular directly (i.e. without the interposition of further elements), to the outlet 8 .
- the area 7 b is arranged between the outlet 8 and the area 7 a.
- the device 2 comprises an outlet duct 9 interposed between the chamber 7 , in particular the area 7 b , and the outlet 8 .
- the device 2 also comprises a second outlet 10 , which is adapted to allow the outlet (of the sample C 1 or) of a substance, in particular at least a portion C 3 of the sample C 1 , from the main chamber 6 and from the device 2 , in particular in a controlled manner.
- the outlet 10 is defined by an outlet nozzle 11 (see in particular FIG. 5 ).
- the device 2 further comprises a reservoir 12 for the sample fluidically connected to the inlet 4 and to the unit 5 , in particular to the chamber 6 .
- the reservoir 12 is arranged between the chamber 6 and the inlet 4 .
- the reservoir 12 is adapted to receive the sample C 1 from the inlet 4 and to direct the sample C 1 towards the unit 5 , in particular towards the chamber 6 .
- the reservoir 12 comprises an inlet duct 13 fluidically connected to the inlet 4 and to the unit 5 , in particular to the chamber 6 . More specifically, the reservoir is formed from the duct 13 .
- the duct 13 comprises a feeding hole 14 at the inlet 4 .
- the duct 13 has a curved configuration (i.e. provided with one or more bends).
- the duct 13 comprises an initial portion 13 a directly connected to the inlet 4 , a terminal portion 13 b directly connected to the unit 5 , in particular to the chamber 6 , and an intermediate portion 13 c arranged between the portions 13 a and 13 b .
- the portions 13 a , 13 b and 13 c have sections with sizes substantially different from one another.
- the device 2 also comprises a collection reservoir 15 adapted to fluidically connect the chamber 6 to the outlet 10 .
- the reservoir 15 is arranged between the chamber 6 and the outlet 10 .
- the reservoir 15 is fluidically, in particular directly and fluidically, connected to the chamber 6 and is adapted to receive at least part of the sample C 1 , in particular at least the portion C 3 , from the chamber 6 and to direct the sample towards (to) the outlet 10 .
- the reservoir 15 comprises, in particular is, a collection duct 16 connected to the chamber 6 . Furthermore, the nozzle 11 is arranged at a final portion 16 a of the collection duct 16 .
- the duct 16 is connected to the chamber 6 at an initial portion 16 b of the duct 16 .
- the portions 16 a and 16 b are arranged at opposite ends of the duct 16 .
- the duct 16 has a curved configuration (i.e. provided with one or more bends).
- the reservoir 15 is absent.
- the device 2 is without a reservoir arranged between the main chamber 6 and the outlet 10 .
- the outflow of substance from the main chamber 6 is facilitated (by reducing the quantity of buffer required for the purpose).
- only one duct 16 with small dimensions (relatively short) is arranged between the main chamber 6 and the outlet 10 .
- the device 2 also comprises a duct 18 adapted to fluidically connect the chamber 7 , in particular the area 7 a , to the outlet 10 .
- the duct 18 is fluidically connected to the chamber 7 , in particular to the area 7 a , and to the duct 16 .
- the device 2 further comprises a reservoir 20 of flushing liquid fluidically connected to the chamber 7 and adapted to receive a flushing liquid, in particular a buffer.
- the device 2 also comprises a second inlet 21 adapted to receive the flushing liquid and to direct the flushing liquid to the reservoir 20 .
- the reservoir 20 is arranged between the inlet 21 and the chamber 7 .
- the reservoir 20 of liquid is connected to a central area 7 c of the chamber 7 interposed between the waiting area 7 a and the recovery area 7 b .
- the reservoir 20 comprises, in particular is, a feeding duct 22 .
- the duct 22 has a second feeding hole 23 arranged at the inlet 21 .
- the reservoir 12 has a volume at least double (in some cases, at least triple) the volume of the chamber 6 (or of the sum of the volumes of the chambers 6 and 7 ).
- the reservoir 20 has a volume at least double (in some cases, at least triple) the volume of the chamber 6 (or of the sum of the volumes of the chambers 6 and 7 ).
- the duct 22 has a curved configuration (i.e. provided with one or more bends).
- the duct 22 comprises a main portion 22 a and an auxiliary portion 22 b ; in particular, the portion 22 b defines a final portion of the duct 22 directly connected to the chamber 7 .
- the portion 22 a has a diameter greater than the portion 22 b . More precisely, the portion 22 a has a section which is substantially greater than the respective sections of the ducts 9 and 13 .
- the device 2 comprises:
- the element 29 has on an own upper surface (visible in FIG. 3 ) at least part of the reservoirs 12 , 15 and 20 , and in particular part of the ducts 13 , 16 , 18 , 22 .
- the element 29 has on an own lower surface (visible in FIGS. 4 and 5 ) at least part of the outlets 8 and 10 , at least part of the inlets 4 and 21 , in particular part of the holes 14 and 23 .
- the device 2 further comprises at least part of a separation group 30 , which comprises the unit 5 .
- This part of the unit 30 is housed in a seat 31 of a housing of the element 29 .
- the apparatus 3 comprises a further part of the separation group 30 , in particular an actuator device.
- the system 1 comprises (therefore) the separation group 30 .
- the device 2 also comprises a plurality of seal elements 32 , in this specific case two, in particular each having an annular shape. More specifically, one of the elements 32 surrounds the hole 14 and the other surrounds the hole 23 .
- the device 2 also comprises a plurality of closing elements 33 , each adapted to collaborate with a respective duct 9 , 13 , 16 , 18 or 21 and forming part of a valve assembly (not illustrated in further detail).
- Each element 33 can be selectively controlled between a closing position in which the respective element 33 fluidically closes the respective duct 9 , 13 , 16 , 18 or 21 and an opening position in which the respective element 33 fluidically opens the respective duct 9 , 13 , 16 , 18 and 21 .
- one of the elements 33 collaborates with the duct 9 so as to selectively close or open the fluidic connection between the outlet 8 and the unit 5 , in particular the chamber 7 .
- Another element 33 collaborates with the duct 13 so as to selectively close or open the fluidic connection between the inlet 4 and the unit 5 , in particular the chamber 6 .
- Another element 33 collaborates with the duct 16 so as to selectively close or open the fluidic connection between the chamber 6 and the outlet 10 .
- Another element 33 collaborates with the duct 18 so as to selectively close or open the fluidic connection between the chamber 7 , in particular the area 7 a and the outlet 10 .
- a further element 33 collaborates with the duct 21 so as to selectively close or open the fluidic connection between the chamber 7 and the inlet 21 .
- the system 1 (in particular, the apparatus 3 ) comprises a detection device 36 adapted to detect the outflow (in particular, the quantity) of a substance, in particular the sample C 1 or at least the portion C 3 of the sample C 1 , from the outlet 10 .
- the detection device 36 comprises:
- the single drops have a predefined volume (in particular known) which substantially depends on the nozzle 11 (and on the liquid). Each drop has substantially the same volume as the others.
- the apparatus 3 also comprises a housing (not illustrated and known per se) to house the device 2 in a removable manner.
- the apparatus 3 further comprises pressure means 38 (more precisely, a pump and/or a reservoir of gas under pressure) adapted to direct the sample from the reservoir 12 to the separation unit 5 .
- pressure means 38 more precisely, a pump and/or a reservoir of gas under pressure
- the system 1 comprises a sensor 37 adapted to detect the passage of a liquid (in particular, of the sample) from the outlet 10 , and a control system (not illustrated and known per se—if necessary comprising the above-mentioned calculation unit) connected to the sensor 37 and adapted to control the pressure means 38 according to the parameters detected by the sensor 37 .
- the control system is adapted to stop the operation of the pressure means 38 when, in use, the sensor 37 detects the passage of liquid.
- the apparatus 3 also comprises pressure means 39 (more precisely, a pump and/or a reservoir of gas under pressure) adapted to direct the flushing liquid from the reservoir 20 to the unit 5 , in particular directly into the chamber 7 .
- pressure means 39 more precisely, a pump and/or a reservoir of gas under pressure
- the system 1 (more precisely, the apparatus 3 ) comprises a recognition device (not illustrated and known per se) adapted to determine the position and type of particles present in the separation unit 5 .
- the recognition device is defined by an apparatus with an optical microscope adapted to obtain an image in fluorescence and/or in bright field to detect the type and positioning of the single particles present in the unit 5 .
- the apparatus with microscope is configured to stimulate selective fluorescence markers with which the particles are labelled and to detect the position of the labelled particles in the unit 5 on the basis of the fluorescence signal received.
- the system 1 (more precisely, the separation group 30 ) comprises the actuator device adapted to move the particles of the specific type from the chamber 6 to the chamber 7 , in particular after the introduction of at least one fraction of the sample C 1 into the unit 5 , in particular into the chamber 6 . More precisely, the actuator device selectively interacts with the specific type particles (with respect to the other particles).
- the actuator device is adapted to actuate the displacement of (i.e. the movement of) the particles of the specific type from the chamber 6 to the chamber 7 in static conditions.
- the actuator device is adapted to displace the particles whereas the sample introduced into the unit 5 , in particular the chamber 6 , is not subject to hydrodynamic movements (flows).
- the separation group 30 (in particular, the actuator device) comprises a system able to exert a force directly on the particles of the specific type (in particular, without the force being exerted on the fluid which transfers the movement to the particles of specific type).
- the separation group 30 (in particular, the actuator device) is adapted to carry out the selective movement of each particle by means of magnetophoresis, dielectrophoresis, acoustic waves (acoustophoresis) and/or optical manipulation (optical tweezers).
- the separation group 30 (in particular, the actuator device) comprises a dielectrophoresis unit (or system) as described for example in at least one of the patent applications WO-A-0069565, WO-A-2007010367, WO-A-2007049120, the contents of which are here referred to in full for completeness of description (incorporated for reference).
- the unit 5 comprises a part of the dielectrophoresis unit (or system). More specifically, the unit 5 (group 30 ) operates according to what is described in the patent applications with publication number WO2010/106434 and WO2012/085884).
- the device 2 is loaded with the sample C 1 and, preferably, also with the flushing liquid.
- the sample C 1 is inserted through the inlet 4 into the reservoir 12 . More specifically, the sample C 1 is inserted in the duct 13 by means of the hole 14 .
- the flushing liquid (in particular a buffer solution) is introduced into the device 2 through the inlet 21 . More precisely, the flushing liquid is introduced into the reservoir 20 . More specifically, the flushing liquid is introduced into the duct 22 by means of the hole 23 .
- the device 2 After loading the sample C 1 and preferably the flushing liquid into the device 2 , the device 2 is inserted into the apparatus 3 , in particular the device 2 is inserted into the housing of the apparatus 3 .
- a fraction of the sample C 1 is transferred from the reservoir 12 (in particular, from the duct 13 ) to the unit 5 , in particular to the chamber 6 .
- the fraction of the sample C 1 is introduced by operation of the pressure means 38 .
- the particles of the specific type are transferred into the chamber 7 in a substantially selective manner with respect to further particles of the sample, in particular by means of a system selected from the group consisting of: dielectrophoresis, optical tweezers, magnetophoresis, acoustophoresis and a combination thereof.
- distribution of the particles in the unit 5 is determined, in particular by means of the recognition device. More specifically, the position and type of each particle is determined. Even more specifically, the particles of the specific type are optically identified on the basis of fluorescent signals (an image is captured or several fluorescence images are captured).
- the particles of the specific type are positioned in the area 7 a of the chamber 7 .
- particles of other types are maintained in the chamber 6 .
- the particles of the specific type are transferred to the area 7 b.
- At least one repetition phase is performed during which the introduction phase and the selection phase are repeated.
- a further fraction of the sample C 1 is introduced from the reservoir 12 , in particular from the duct 13 , into the unit 5 .
- the particles of the specific type are then re-positioned in the chamber 7 , in particular in the area 7 a.
- the discharge phase is also repeated. In this way it is possible to process a greater number of particles than the number that can be managed by the system 1 ; more precisely, in this way it is possible to process a greater number of particles than the number that can be contained in the waiting area 7 a.
- fractions of the sample can flow out of the outlet 10 and are collected outside the device 2 .
- at least a portion C 3 of the sample flows out of the chamber 6 and the device 2 through the outlet 10 .
- the portion C 3 of the sample C 1 is at least part of the fraction of the sample C 1 introduced into the unit 5 in the preceding phase.
- the repetition phase/s is/are particularly useful when the sample C 1 contains a particularly high quantity of particles (and therefore has to be very diluted), more precisely, when the cells of interest are a very low percentage with respect to the total cells.
- At least one discharge phase is also scheduled, during which the particles of the specific type are conveyed from the chamber 7 outside the device 2 through the outlet 8 .
- the particles of the specific type are collected in the final sample C 2 (which passes through the outlet 8 ).
- the particles contained in said final sample C 2 subsequently undergo further analyses.
- the discharge phase is performed by introducing the flushing liquid into the chamber 7 .
- the flushing liquid is transferred from the reservoir 20 (in particular, from the duct 22 ) into the chamber 7 .
- the pressure means 39 are operated to direct the flushing liquid from the duct 22 into the chamber 7 .
- the discharge phase is performed only at the end of the (of all the) repetition phases.
- a respective discharge phase is performed at the end of each repetition phase (or at the end of a part of the repetition phases).
- an outflow phase is performed, in particular to remove the remaining fraction of the sample C 1 in the chamber 6 from said chamber 6 (and to recover the remaining fraction of the sample outside the device 2 ).
- the flushing liquid is introduced into the chamber 6 .
- the pressure means 39 are operated to direct the flushing liquid from the reservoir 20 through the (part of the) chamber 7 to the chamber 6 .
- the outflow phase is subsequent to the selection phase and prior to the discharge phase.
- a first fluid is caused to flow into the separation unit 5 , entering into the (in particular, through the) main chamber 6 and a second fluid is caused to flow into the separation unit 5 , entering into the (in particular, through the) recovery chamber 7 .
- the system 1 comprises a reservoir 12 , which is fluidically connected to the separation unit 5 at (in particular, through) the main chamber 6 and is in particular adapted to contain the sample; and pressure means 38 , adapted to direct a first fluid from the reservoir 12 into the main chamber 6 .
- the system 1 further comprises a second reservoir 20 , which is fluidically connected to the separation unit 5 at the (in particular, through the) recovery chamber 7 and is in particular adapted to contain a flushing liquid; and pressure means 39 , adapted to direct a second fluid from the second reservoir 20 into the main chamber 6 .
- the pressure means 38 and 39 are operated.
- the reservoir 12 has relatively small dimensions. To perform one or more repetition phases, the reservoir 12 has a different shape and (above all) a significantly higher containment capacity (volume) than the reservoir 12 illustrated.
- the reservoir 12 has a volume at least twice (in some cases, at least three times) the volume of the chamber 6 (or of the sum of the volumes of chambers 6 and 7 ).
- the particles of the specific type are optically identified on the basis of fluorescent signals (coming from the particles).
- the device 2 is able to recover all (or almost all) the sample C 1 . Subsequently, it is therefore possible to introduce the sample into a new device 2 in order to then isolate the particles of the specific type by means of the new device 2 .
- a further advantage lies in the fact that, due to the presence of the second outlet 10 and, therefore, the possibility of repeating the introduction and selection phases several times, it is possible to obtain a final sample substantially comprising all the particles of the specific type also in samples containing a high number of particles, in particular when the sample has a low percentage of particles of interest with respect to the total particles (for example below 1/1000) and/or when it is necessary to obtain a high number of particles of interest.
- hydrophobic membrane has been eliminated and with it, also the possible problem of an undesired and uncontrolled outflow of a fraction of the sample C 1 or of another substance from the device 2 due to rupture of the hydrophobic membrane.
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- Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
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Abstract
Description
- The present invention concerns a microfluidic device, a microfluidic system and a method for isolating particles of a sample, in particular a biological sample.
- Systems for the isolation of particles of at least one specific type of a sample, in particular a biological sample in liquid form are known. These systems receive, in use, a sample comprising particles of the specific type and typically particles of one or more different types and are adapted to select and separate the particles of the specific type and the particles of the different type or types. Generally, these systems allow not only the isolation of the particles of the specific type belonging to a sample comprising also other types of particles, but also recognition of the various particles before their isolation.
- These systems can be applied, for example, in the analysis of biological samples comprising tumour cells, foetal cells, stem cells or other types of cells.
- A system of this type is described in EP-A-2408562 and comprises an analysis apparatus and a microfluidic device (in particular, a cartridge) for isolation of the particles of the specific type.
- The microfluidic device for the isolation of particles, which is of the disposable type, is, in use, housed in the apparatus in a removable manner.
- The microfluidic device is provided with a first inlet through which, in use, a sample comprising the particles is introduced into the microfluidic device, a separation unit, which comprises a main chamber and a recovery chamber fluidically connected to each other, and an inlet duct connected to the first inlet and to the main chamber.
- In use, the particles of the specific type are transferred, in a selective manner with respect to particles of a different type, into the recovery chamber, which comprises a waiting area and a recovery area.
- The device further comprises an outlet connected by means of an outlet duct to the recovery chamber, more specifically to the recovery area. In use, the particles of the specific type are discharged from the recovery chamber, more specifically from the recovery area and from the microfluidic device, through the first duct and the outlet.
- The microfluidic device also comprises a second inlet, which is connected by means of a feeding duct to the recovery chamber and through which, in use, a flushing liquid is introduced into the recovery chamber.
- The microfluidic device further comprises a collection reservoir connected to the main chamber and to the waiting area. A hydrophobic membrane is also provided arranged at a terminal portion of the collection reservoir, said membrane allowing outflow of the air present in the microfluidic device and, when intact, preventing outflow of the sample or of parts of the sample and/or of the sample.
- Furthermore, the apparatus comprises a first pump, which is adapted to direct the sample through the inlet duct into the separation unit, and a second pump, which is adapted to direct the flushing liquid into the recovery chamber.
- The system further comprises a recognition device having a fluorescence microscope, which allows the recognition of the types of particles and the determination of the relative positions, and an actuator device, which allows the particles to be moved according to the type of particles recognised by the recognition device so as to convey the particles of the specific type into the recovery chamber and maintain the particles of different type in the main chamber. More specifically, the actuator device is adapted to displace the particles by means of dielectrophoresis.
- A microfluidic system of this type is described in EP-A-2408562 and does not allow (or allows only to a limited extent) the introduction of several successive portions of the sample into the separation unit. In particular, if there are large quantities of a sample, it is not possible to isolate all the particles of the specific type using one single microfluidic device; more than one device has to be used. This prolongs working times and increases costs.
- A further drawback lies in the fact that a malfunction of the hydrophobic membrane (for example a rupture) can cause outflow of the sample from the microfluidic device, which may damage the apparatus and/or the system.
- It should be further noted that when using the known microfluidic systems, it is not possible to recover the sample once it has been introduced into the microfluidic device.
- The object of the present invention is to provide a microfluidic device, a microfluidic system and a method for the isolation of particles which overcome, at least partially, the drawbacks of the known art and are, at the same time, easy and inexpensive to produce.
- According to the present invention, a microfluidic device, a microfluidic system and a method for the isolation of particles are provided, as claimed in the following independent claims and, preferably, in any one of the claims depending directly or indirectly on the independent claims.
- Unless explicitly specified otherwise, in this text the following terms have the meaning as indicated below.
- By equivalent diameter of a section we mean the diameter of a circle having the same area as the section.
- By microfluidic system we mean a system comprising at least one microfluidic duct and/or at least one microfluidic chamber. In particular, the microfluidic system comprises at least one pump (more specifically, a plurality of pumps), at least one valve assembly (more specifically, a plurality of valve assemblies) and if necessary at least one gasket (more specifically, a plurality of gaskets).
- In the context of the present patent application, a reservoir can comprise a microfluidic duct, a microfluidic chamber or any combination thereof.
- In particular, by microfluidic duct we mean a duct having a section with an equivalent diameter smaller than 0.5 mm.
- In particular, the microfluidic chamber has a height of less than 0.5 mm. More specifically, the microfluidic chamber has a width and a length greater than the height (more precisely at least five times the height).
- In the present text, by particle we mean a corpuscle having its largest dimension of less than 500 μm (advantageously less than 150 μm). Non-limiting examples of particles are: cells, cell debris (in particular, cell fragments), cell aggregates (e.g. small clusters of cells deriving from stem cells like neurospheres or mammospheres), bacteria, lipospheres, microspheres (in polystyrene and/or magnetic), complex nanospheres (e.g. nanospheres up to 100 nm) formed of microspheres bound to cells. Advantageously, the particles are cells.
- According to some embodiments, the largest dimension of the particles (advantageously cells and/or cell debris) is smaller than 60 μm.
- The dimensions of the particles can be measured in a standard way by microscopes with a graduated scale or normal microscopes used with slides (on which the particles are deposited) with a graduated scale.
- In the present text, by dimensions of a particle we mean the length, width and thickness of the particle.
- The term “selective” is used to identify a movement (or other analogous terms indicating a movement and/or a separation and/or a displacement) of particles, in which the particles that are moved and/or separated and/or displaced are particles largely of one or more specific types. Advantageously, a movement (or other analogous terms indicating a movement and/or a separation and/or a displacement) which is substantially selective entails moving particles with at least 90% (advantageously 95%) of particles of specific type/s (percentage given by the number of particles of the specific type/s with respect to the number of overall particles).
- The present invention will now be described with reference to the accompanying drawings, which illustrate a non-limiting example embodiment thereof, in which:
-
FIG. 1 schematically illustrates a system produced according to the present invention; -
FIG. 2 is a view from above of a device of the system ofFIG. 1 ; -
FIG. 3 is a view from above of an exploded drawing of the device ofFIG. 2 ; -
FIG. 4 is a view from below of an exploded drawing of the device ofFIG. 2 ; and -
FIG. 5 is an enlarged view of a detail ofFIG. 4 . - In
FIG. 1 ,number 1 indicates schematically and overall amicrofluidic system 1 for the isolation of particles of at least one specific type belonging to a sample C1. Thesystem 1 comprises amicrofluidic device 2 for the isolation of the particles of the specific type and an apparatus 3 (only partially illustrated) adapted to house thedevice 2, in particular in a removable manner, and to cooperate with thedevice 2 for isolation of the particles of specific type. - According to some non-limiting embodiments, the
system 1 is adapted to isolate a specific type of particle. Thesystem 1 can also be used for the isolation of different types of particles. - It should be noted that the sample typically comprises the particles of the specific type and at least one other type of particle. More precisely, the sample is a biological sample and, in particular, is a suspension of biological cells (for example cells).
- In particular, the
system 1 is adapted to isolate the particles of the specific type in a substantially selective manner with respect to the particles of the other type or other types. More specifically, thesystem 1 is adapted to isolate the particles of the specific type from the other type of particles so as to obtain a final sample C2 adapted to be further analysed, in particular by means of biological analysis. - Advantageously, the
device 2 is a disposable cartridge. - With particular reference to
FIGS. 1 and 2 , and according to an aspect of the present invention, thedevice 2 comprises: -
- a
first inlet 4 adapted to receive the sample C1 comprising the particles of the specific type for introduction of the sample C1 into thedevice 2; - a
separation unit 5, which comprises amain chamber 6 and arecovery chamber 7 and is adapted to receive the sample C1 and to transfer at least part of the particles of the specific type from themain chamber 6 to therecovery chamber 7 in a substantially selective manner with respect to further particles of the sample C1; and - a first outlet 8 (fluidically connected, in particular directly, to the
chamber 7 and) configured to allow collection of the particles of the specific type, in particular in a final sample C2, outside of thedevice 2.
- a
- In greater detail, the
chamber 7 of theunit 5 comprises awaiting area 7 a and arecovery area 7 b fluidically connected to each other and to thechamber 6. Thearea 7 b is fluidically connected, in particular directly (i.e. without the interposition of further elements), to theoutlet 8. In particular, thearea 7 b is arranged between theoutlet 8 and thearea 7 a. - In further detail, the
device 2 comprises anoutlet duct 9 interposed between thechamber 7, in particular thearea 7 b, and theoutlet 8. - Advantageously, the
device 2 also comprises asecond outlet 10, which is adapted to allow the outlet (of the sample C1 or) of a substance, in particular at least a portion C3 of the sample C1, from themain chamber 6 and from thedevice 2, in particular in a controlled manner. In particular, theoutlet 10 is defined by an outlet nozzle 11 (see in particularFIG. 5 ). - According to some non-limiting embodiments, the
device 2 further comprises areservoir 12 for the sample fluidically connected to theinlet 4 and to theunit 5, in particular to thechamber 6. In particular, thereservoir 12 is arranged between thechamber 6 and theinlet 4. - More precisely, the
reservoir 12 is adapted to receive the sample C1 from theinlet 4 and to direct the sample C1 towards theunit 5, in particular towards thechamber 6. - According to some non-limiting embodiments (like the one illustrated), the
reservoir 12 comprises aninlet duct 13 fluidically connected to theinlet 4 and to theunit 5, in particular to thechamber 6. More specifically, the reservoir is formed from theduct 13. Preferably, theduct 13 comprises afeeding hole 14 at theinlet 4. Advantageously but not necessarily, theduct 13 has a curved configuration (i.e. provided with one or more bends). Furthermore, theduct 13 comprises aninitial portion 13 a directly connected to theinlet 4, aterminal portion 13 b directly connected to theunit 5, in particular to thechamber 6, and anintermediate portion 13 c arranged between theportions portions - Advantageously but not necessarily, the
device 2 also comprises acollection reservoir 15 adapted to fluidically connect thechamber 6 to theoutlet 10. In particular, thereservoir 15 is arranged between thechamber 6 and theoutlet 10. - In greater detail, the
reservoir 15 is fluidically, in particular directly and fluidically, connected to thechamber 6 and is adapted to receive at least part of the sample C1, in particular at least the portion C3, from thechamber 6 and to direct the sample towards (to) theoutlet 10. - More precisely, the
reservoir 15 comprises, in particular is, acollection duct 16 connected to thechamber 6. Furthermore, thenozzle 11 is arranged at afinal portion 16 a of thecollection duct 16. Theduct 16 is connected to thechamber 6 at aninitial portion 16 b of theduct 16. Theportions duct 16. In some embodiments, theduct 16 has a curved configuration (i.e. provided with one or more bends). - According to alternative embodiments, the
reservoir 15 is absent. In other words, thedevice 2 is without a reservoir arranged between themain chamber 6 and theoutlet 10. In this way, the outflow of substance from themain chamber 6 is facilitated (by reducing the quantity of buffer required for the purpose). In particular, in these cases, only oneduct 16 with small dimensions (relatively short) is arranged between themain chamber 6 and theoutlet 10. - Advantageously but not necessarily, the
device 2 also comprises aduct 18 adapted to fluidically connect thechamber 7, in particular thearea 7 a, to theoutlet 10. In particular, theduct 18 is fluidically connected to thechamber 7, in particular to thearea 7 a, and to theduct 16. - In particular, the
device 2 further comprises areservoir 20 of flushing liquid fluidically connected to thechamber 7 and adapted to receive a flushing liquid, in particular a buffer. Thedevice 2 also comprises asecond inlet 21 adapted to receive the flushing liquid and to direct the flushing liquid to thereservoir 20. In particular, thereservoir 20 is arranged between theinlet 21 and thechamber 7. - In greater detail, the
reservoir 20 of liquid is connected to acentral area 7 c of thechamber 7 interposed between the waitingarea 7 a and therecovery area 7 b. Thereservoir 20 comprises, in particular is, a feedingduct 22. Theduct 22 has asecond feeding hole 23 arranged at theinlet 21. - In particular, the
reservoir 12 has a volume at least double (in some cases, at least triple) the volume of the chamber 6 (or of the sum of the volumes of thechambers 6 and 7). - Advantageously but not necessarily, the
reservoir 20 has a volume at least double (in some cases, at least triple) the volume of the chamber 6 (or of the sum of the volumes of thechambers 6 and 7). - Furthermore, preferably, the
duct 22 has a curved configuration (i.e. provided with one or more bends). - In further detail, the
duct 22 comprises amain portion 22 a and anauxiliary portion 22 b; in particular, theportion 22 b defines a final portion of theduct 22 directly connected to thechamber 7. In particular, theportion 22 a has a diameter greater than theportion 22 b. More precisely, theportion 22 a has a section which is substantially greater than the respective sections of theducts - According to some embodiments (like the one illustrated in
FIGS. 3 and 4 ), thedevice 2 comprises: -
- an
upper element 27, in particular made of COC (cyclic olefin copolymer) or a similar material; - a
support element 28, in particular made of COC (cyclic olefin copolymer) or a similar material or is a printed circuit; and - an
intermediate element 29, in particular made of polymethyl methacrylate (PMMA) or a similar material, interposed between theelements
- an
- More precisely, the
element 29 has on an own upper surface (visible inFIG. 3 ) at least part of thereservoirs ducts element 29 has on an own lower surface (visible inFIGS. 4 and 5 ) at least part of theoutlets inlets holes - In particular, the
device 2 further comprises at least part of aseparation group 30, which comprises theunit 5. This part of theunit 30 is housed in aseat 31 of a housing of theelement 29. According to some embodiments, theapparatus 3 comprises a further part of theseparation group 30, in particular an actuator device. Thesystem 1 comprises (therefore) theseparation group 30. - According to one embodiment, the
device 2 also comprises a plurality ofseal elements 32, in this specific case two, in particular each having an annular shape. More specifically, one of theelements 32 surrounds thehole 14 and the other surrounds thehole 23. - According to one embodiment, the
device 2 also comprises a plurality of closingelements 33, each adapted to collaborate with arespective duct element 33 can be selectively controlled between a closing position in which therespective element 33 fluidically closes therespective duct respective element 33 fluidically opens therespective duct - In further detail, one of the
elements 33 collaborates with theduct 9 so as to selectively close or open the fluidic connection between theoutlet 8 and theunit 5, in particular thechamber 7. Anotherelement 33 collaborates with theduct 13 so as to selectively close or open the fluidic connection between theinlet 4 and theunit 5, in particular thechamber 6. Anotherelement 33 collaborates with theduct 16 so as to selectively close or open the fluidic connection between thechamber 6 and theoutlet 10. Anotherelement 33 collaborates with theduct 18 so as to selectively close or open the fluidic connection between thechamber 7, in particular thearea 7 a and theoutlet 10. Afurther element 33 collaborates with theduct 21 so as to selectively close or open the fluidic connection between thechamber 7 and theinlet 21. - Advantageously but not necessarily, with particular reference to
FIG. 1 , the system 1 (in particular, the apparatus 3) comprises adetection device 36 adapted to detect the outflow (in particular, the quantity) of a substance, in particular the sample C1 or at least the portion C3 of the sample C1, from theoutlet 10. - More precisely, the
detection device 36 comprises: -
- a
sensor 37 adapted to detect single drops of the substance, in particular the sample C1 or at least the portion C3 of the sample C1 which, in use, flows out of theoutlet 10, in particular which flows out of theoutlet 10 in a controlled manner; and - a calculation unit (not illustrated and known per se) adapted to determine the quantity of the substance (in particular of the sample C1 or at least of the portion C3 of the sample C1) which flows out of the
outlet 10 according to the number of single drops detected by thesensor 37.
- a
- It should be noted that the single drops have a predefined volume (in particular known) which substantially depends on the nozzle 11 (and on the liquid). Each drop has substantially the same volume as the others.
- Preferably, the
apparatus 3 also comprises a housing (not illustrated and known per se) to house thedevice 2 in a removable manner. - In particular, the
apparatus 3 further comprises pressure means 38 (more precisely, a pump and/or a reservoir of gas under pressure) adapted to direct the sample from thereservoir 12 to theseparation unit 5. - In addition or alternatively, according to some non-limiting embodiments, the
system 1 comprises asensor 37 adapted to detect the passage of a liquid (in particular, of the sample) from theoutlet 10, and a control system (not illustrated and known per se—if necessary comprising the above-mentioned calculation unit) connected to thesensor 37 and adapted to control the pressure means 38 according to the parameters detected by thesensor 37. In particular, the control system is adapted to stop the operation of the pressure means 38 when, in use, thesensor 37 detects the passage of liquid. - In addition or alternatively, the
apparatus 3 also comprises pressure means 39 (more precisely, a pump and/or a reservoir of gas under pressure) adapted to direct the flushing liquid from thereservoir 20 to theunit 5, in particular directly into thechamber 7. - According to some embodiments, the system 1 (more precisely, the apparatus 3) comprises a recognition device (not illustrated and known per se) adapted to determine the position and type of particles present in the
separation unit 5. - Advantageously but not necessarily, the recognition device is defined by an apparatus with an optical microscope adapted to obtain an image in fluorescence and/or in bright field to detect the type and positioning of the single particles present in the
unit 5. In particular, the apparatus with microscope is configured to stimulate selective fluorescence markers with which the particles are labelled and to detect the position of the labelled particles in theunit 5 on the basis of the fluorescence signal received. - Advantageously but not necessarily, the system 1 (more precisely, the separation group 30) comprises the actuator device adapted to move the particles of the specific type from the
chamber 6 to thechamber 7, in particular after the introduction of at least one fraction of the sample C1 into theunit 5, in particular into thechamber 6. More precisely, the actuator device selectively interacts with the specific type particles (with respect to the other particles). - In greater detail, the actuator device is adapted to actuate the displacement of (i.e. the movement of) the particles of the specific type from the
chamber 6 to thechamber 7 in static conditions. In other words, the actuator device is adapted to displace the particles whereas the sample introduced into theunit 5, in particular thechamber 6, is not subject to hydrodynamic movements (flows). - According to some advantageous and non-limiting embodiments, the separation group 30 (in particular, the actuator device) comprises a system able to exert a force directly on the particles of the specific type (in particular, without the force being exerted on the fluid which transfers the movement to the particles of specific type).
- The separation group 30 (in particular, the actuator device) is adapted to carry out the selective movement of each particle by means of magnetophoresis, dielectrophoresis, acoustic waves (acoustophoresis) and/or optical manipulation (optical tweezers). According to specific embodiments, the separation group 30 (in particular, the actuator device) comprises a dielectrophoresis unit (or system) as described for example in at least one of the patent applications WO-A-0069565, WO-A-2007010367, WO-A-2007049120, the contents of which are here referred to in full for completeness of description (incorporated for reference). In particular, the
unit 5 comprises a part of the dielectrophoresis unit (or system). More specifically, the unit 5 (group 30) operates according to what is described in the patent applications with publication number WO2010/106434 and WO2012/085884). - In use, before insertion of the
device 2 into theapparatus 3, thedevice 2 is loaded with the sample C1 and, preferably, also with the flushing liquid. In particular, the sample C1 is inserted through theinlet 4 into thereservoir 12. More specifically, the sample C1 is inserted in theduct 13 by means of thehole 14. - Furthermore, prior to insertion of the
device 2 into theapparatus 3, the flushing liquid (in particular a buffer solution) is introduced into thedevice 2 through theinlet 21. More precisely, the flushing liquid is introduced into thereservoir 20. More specifically, the flushing liquid is introduced into theduct 22 by means of thehole 23. - After loading the sample C1 and preferably the flushing liquid into the
device 2, thedevice 2 is inserted into theapparatus 3, in particular thedevice 2 is inserted into the housing of theapparatus 3. - At this point, during an introduction phase, at least one fraction of the sample C1 is inserted into the
unit 5. In particular, a fraction of the sample C1 is transferred from the reservoir 12 (in particular, from the duct 13) to theunit 5, in particular to thechamber 6. More specifically, the fraction of the sample C1 is introduced by operation of the pressure means 38. - At this point, in particular, after the introduction phase, during at least one selection phase, the particles of the specific type are transferred into the
chamber 7 in a substantially selective manner with respect to further particles of the sample, in particular by means of a system selected from the group consisting of: dielectrophoresis, optical tweezers, magnetophoresis, acoustophoresis and a combination thereof. - Advantageously but not necessarily, during the selection phase, distribution of the particles in the
unit 5 is determined, in particular by means of the recognition device. More specifically, the position and type of each particle is determined. Even more specifically, the particles of the specific type are optically identified on the basis of fluorescent signals (an image is captured or several fluorescence images are captured). - More specifically, this occurs by activation of the actuator device substantially as described in the patent applications WO-A-0069565, WO-A-2007010367 and WO-A-2007049120.
- More specifically, the particles of the specific type are positioned in the
area 7 a of thechamber 7. Typically, particles of other types are maintained in thechamber 6. Subsequently, in particular prior to a discharge phase of the particles of specific type, the particles of the specific type are transferred to thearea 7 b. - According to some non-limiting embodiments, at least one repetition phase is performed during which the introduction phase and the selection phase are repeated. In particular, a further fraction of the sample C1 is introduced from the
reservoir 12, in particular from theduct 13, into theunit 5. The particles of the specific type are then re-positioned in thechamber 7, in particular in thearea 7 a. - In some cases, during the repetition phase, the discharge phase is also repeated. In this way it is possible to process a greater number of particles than the number that can be managed by the
system 1; more precisely, in this way it is possible to process a greater number of particles than the number that can be contained in the waitingarea 7 a. - Advantageously but not necessarily, several repetition phases are performed so as to process all the sample C1 to obtain a final sample substantially comprising all the particles of the specific type originally present in the sample C1.
- Furthermore, advantageously, during the repetition phases, fractions of the sample can flow out of the
outlet 10 and are collected outside thedevice 2. Advantageously, but not necessarily, during the repetition phase or phases, while the further fraction of the sample C1 is introduced into theunit 5, at least a portion C3 of the sample flows out of thechamber 6 and thedevice 2 through theoutlet 10. In particular, the portion C3 of the sample C1 is at least part of the fraction of the sample C1 introduced into theunit 5 in the preceding phase. - The repetition phase/s is/are particularly useful when the sample C1 contains a particularly high quantity of particles (and therefore has to be very diluted), more precisely, when the cells of interest are a very low percentage with respect to the total cells.
- At least one discharge phase is also scheduled, during which the particles of the specific type are conveyed from the
chamber 7 outside thedevice 2 through theoutlet 8. In particular, the particles of the specific type are collected in the final sample C2 (which passes through the outlet 8). The particles contained in said final sample C2 subsequently undergo further analyses. - More specifically, the discharge phase is performed by introducing the flushing liquid into the
chamber 7. In particular, the flushing liquid is transferred from the reservoir 20 (in particular, from the duct 22) into thechamber 7. More specifically, the pressure means 39 are operated to direct the flushing liquid from theduct 22 into thechamber 7. - In some cases, which entail several repetition phases, the discharge phase is performed only at the end of the (of all the) repetition phases.
- In other cases, which entail several repetition phases, a respective discharge phase is performed at the end of each repetition phase (or at the end of a part of the repetition phases).
- Advantageously but not necessarily, before each repetition phase an outflow phase is performed, in particular to remove the remaining fraction of the sample C1 in the
chamber 6 from said chamber 6 (and to recover the remaining fraction of the sample outside the device 2). - In greater detail, during the outflow phase at least part of the sample is conveyed from the
chamber 6 through the outlet 10 (and outside the device 2). In particular, during the outlet phase, the flushing liquid is introduced into thechamber 6. More specifically, during the outlet phase, the pressure means 39 are operated to direct the flushing liquid from thereservoir 20 through the (part of the)chamber 7 to thechamber 6. - Advantageously but not necessarily, the outflow phase is subsequent to the selection phase and prior to the discharge phase.
- According to some embodiments, during the outlet phase, to convey at least part of the sample C1 through the
outlet 10, a first fluid is caused to flow into theseparation unit 5, entering into the (in particular, through the)main chamber 6 and a second fluid is caused to flow into theseparation unit 5, entering into the (in particular, through the)recovery chamber 7. - In some cases, the
system 1 comprises areservoir 12, which is fluidically connected to theseparation unit 5 at (in particular, through) themain chamber 6 and is in particular adapted to contain the sample; and pressure means 38, adapted to direct a first fluid from thereservoir 12 into themain chamber 6. Thesystem 1 further comprises asecond reservoir 20, which is fluidically connected to theseparation unit 5 at the (in particular, through the)recovery chamber 7 and is in particular adapted to contain a flushing liquid; and pressure means 39, adapted to direct a second fluid from thesecond reservoir 20 into themain chamber 6. In these cases, during the outflow phase, the pressure means 38 and 39 are operated. - It should be noted that in the embodiment illustrated in the figures (in particular, see
FIG. 2 ), thereservoir 12 has relatively small dimensions. To perform one or more repetition phases, thereservoir 12 has a different shape and (above all) a significantly higher containment capacity (volume) than thereservoir 12 illustrated. - In particular, the
reservoir 12 has a volume at least twice (in some cases, at least three times) the volume of the chamber 6 (or of the sum of the volumes ofchambers 6 and 7). - According to some non-limiting embodiments, during the selection phase, the particles of the specific type are optically identified on the basis of fluorescent signals (coming from the particles).
- It should be noted that, according to the present invention, important advantages are obtained with respect to the state of the art. In particular, it is underlined that the presence of the
second outlet 10, in particular of thenozzle 11, allows recovery of the sample C1 or at least of the portion C3 of the sample C1. This is particularly advantageous considering that the sample C1 is difficult to recover and that it has a high value. In particular, in some application cases the sample C1 serves to diagnose serious illnesses. The loss of samples could, therefore, result in very negative consequences for the patients. - Furthermore, also in the case of a malfunction of the
device 2 which does not allow the isolation of the specific particles, thedevice 2 is able to recover all (or almost all) the sample C1. Subsequently, it is therefore possible to introduce the sample into anew device 2 in order to then isolate the particles of the specific type by means of thenew device 2. - A further advantage lies in the fact that, due to the presence of the
second outlet 10 and, therefore, the possibility of repeating the introduction and selection phases several times, it is possible to obtain a final sample substantially comprising all the particles of the specific type also in samples containing a high number of particles, in particular when the sample has a low percentage of particles of interest with respect to the total particles (for example below 1/1000) and/or when it is necessary to obtain a high number of particles of interest. - Furthermore, the hydrophobic membrane has been eliminated and with it, also the possible problem of an undesired and uncontrolled outflow of a fraction of the sample C1 or of another substance from the
device 2 due to rupture of the hydrophobic membrane. - Unless explicitly indicated otherwise, the contents of the references (articles, books, patent applications etc.) cited in this text are referred to here in full. In particular the above-mentioned references are incorporated here for reference.
Claims (40)
Applications Claiming Priority (5)
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IT102016000104645A IT201600104645A1 (en) | 2016-10-18 | 2016-10-18 | MICROFLUIDIC DEVICE AND METHOD FOR INSULATING PARTICLES |
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IT1309430B1 (en) | 1999-05-18 | 2002-01-23 | Guerrieri Roberto | METHOD AND APPARATUS FOR HANDLING PARTICLES BY MEANS OF ELECTROPHORESIS |
US7485454B1 (en) * | 2000-03-10 | 2009-02-03 | Bioprocessors Corp. | Microreactor |
US20110177547A1 (en) * | 2004-12-10 | 2011-07-21 | Arryx, Inc. | Particle Sorting Using Fluid Streams |
KR20060111143A (en) | 2005-04-22 | 2006-10-26 | 한국표준과학연구원 | Apparatus for separating particles using optical trapping |
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SG10202103867PA (en) | 2021-05-28 |
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CA3039857A1 (en) | 2018-04-26 |
CN109843438B (en) | 2022-07-12 |
EP3528949A1 (en) | 2019-08-28 |
AU2022235560B2 (en) | 2024-06-20 |
KR102637616B1 (en) | 2024-02-16 |
JP7029461B2 (en) | 2022-03-03 |
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AU2017345507A1 (en) | 2019-05-09 |
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